EP0086306A1 - Système de formation d'images pour la projection sélective de matériau utilisant la RMN - Google Patents

Système de formation d'images pour la projection sélective de matériau utilisant la RMN Download PDF

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EP0086306A1
EP0086306A1 EP82306733A EP82306733A EP0086306A1 EP 0086306 A1 EP0086306 A1 EP 0086306A1 EP 82306733 A EP82306733 A EP 82306733A EP 82306733 A EP82306733 A EP 82306733A EP 0086306 A1 EP0086306 A1 EP 0086306A1
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volume
projection
plane
signal
excitation
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EP0086306B1 (fr
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Albert Macovski
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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
    • G01R33/48—NMR imaging systems
    • G01R33/50—NMR imaging systems based on the determination of relaxation times, e.g. T1 measurement by IR sequences; T2 measurement by multiple-echo sequences
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
    • G01R33/48—NMR imaging systems
    • G01R33/54—Signal processing systems, e.g. using pulse sequences ; Generation or control of pulse sequences; Operator console
    • G01R33/56—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution

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  • This invention relates to medical imaging systems using nuclear magnetic resonance.
  • the invention relates to projection imaging of specific materials having unique NMR properties.
  • Nuclear magnetic resonance abbreviated NMR
  • NMR Nuclear magnetic resonance
  • magnetic moments are excited at specific spin frequencies which are proportional to the local magnetic field.
  • the radio frequency signals resulting from the decay of these spins are received using pick-up coils.
  • pick-up coils By manipulating the magnetic fields, an array of signals are provided representing different regions of the volume. These are combined to produce a volumetric image of the density of the body.
  • the projection image is obtained by obtaining the integrated density of substantially all planes which are normal to the plane of the projection image.
  • the total number of planes required, at all angles and positions, is substantially equal to the number of pixels in the two-dimensional projection image.
  • the reconstruction procedure involves the classical reconstruction from projections widely used in current computerized tomography systems. The most generally used procedure is that of convolution-back projection.
  • the resultant two-dimensional projection images have a number of drawbacks and, as a result, are not used. Firstly, the superimposed intervening structures make it very difficult to visualize the desired structure, be it an organ or tumor. Secondly, the nature of this imaging procedure is such that all of the measurements affect every reconstructed pixel. This makes the image particularly sensitive to motion. Any motion of the object will cause artifacts in the image due to inconsistencies where the object does not match its projections. These artifacts can often obscure the desired information.
  • cross-sectional images are free of intervening structures. They are unsuitable for many medical problems.
  • the cross-sectional format is often difficult to interpret.
  • acquisition of three-dimensional data takes a relatively long time, thus resulting in a variety of artifacts due to the various physiological motions of the body.
  • a second general method of acquiring and processing NMR imaging data is described in a paper by E.R. Andrew entitled “Nuclear Magnetic Resonance Imaging: The. Multiple Sensitive Point Method” pp. 1232 to 123B of the same issue.
  • a selective system is used which acquires data from individual voxels in the volume of interest. This is accomplished using dynamically varying fields for the gradients.
  • these dynamic flelds all but the small region not containing the time-varying field integrates to zero.
  • time varying fields of different frequencies are applied to three orthogonal axes, only a single point or voxel will not be time varying. The signal will therefore represent solely that point without requiring reconstruction from projections.
  • this method avoids the motion artifacts caused by reconstruction from projections, it continues to provide a relatively long data acquisition time with the reaulting blurriug from physiological motions including respiratory and cardiovascular.
  • it is a three-dimensional imaging system which provides cross-sectional images.
  • a third imaging method is also line or point selective and is described in a paper by L.E. Crooks entitled, "Selective Irradiation Line Scan Techniques for NMR imaging" of pp. 1239-1244 of the same issue.
  • This general approach has a number of variations.
  • a selective pulse is used to excite a single plane of interest using a static gradient and an appropriately shaped pulse. The resulting signal from the excited plane is stored. Following equilibrium an orthogonal plane is excited with a higher intensity such that the magnetization is inverted or made negative. Irradiation of this type produces no received signal.
  • the first step is then repeated by selectively exciting the plane of interest and storing the resultant signal.
  • each plane integral is phase encoded by applying a gradient normal to the plane. When the gradient is removed, the nuclei along the plane have cyclical phase distributions, depending on the strength of the magnetic field.
  • phase distributions With different spatial frequencies, information is acquired about each line in the plane. This information is decoded again using Fourier transforms. This approach has been termed spin warp imaging.
  • Each of the data acquisition systems described can be used to measure density, the longitudinal relaxation time T 1 and the spin-spin relaxation time T 2 .
  • the density information can be acquired using an excitation which rotates the magnetic moment by 90°, and measuring the free induction decay or FID signal.
  • T 1 can be measured by inverting the magnetic moment with a 180° excitation, and then following it with a 90° excitation whereby the resultant signal will be determined by the amount of decay.
  • two 90° excitations, separated by a time less than 4T 1 will result in signals whose amplitude differences can be used to determine T 1 .
  • the decay time of the FID signal cannot directly be used to measure T 2 since the inhomogeneity of the fields cause a rapid decay. However, if 180" inversion excitations are periodically applied, these serve to cancel the effects of the field inhomogeneity. If the amplitudes of the spin echoes following these inversion excitations are observed and compared to the initial FID signal following the 90° excitation, the decay is indicative of T 2 .
  • a variety of equivalent methods have been described for the measuring of the components. Cross-sectional images have been made of each of these components.
  • An object of this invention is to provide NMR projection images of specific materials within the body.
  • a further object of this invention is to provide isolated NMR projection images of the body with substantially reduced data acquisition time.
  • a further object of this invention is to provide NMR images with reduced sensitivity to image artifacts.
  • a further object of this invention is to provide NMR projection images
  • a further object of this invention is to provide NMR images with substantially higher resolution.
  • a further object of this invention is to provide NMR images of materials other than hydrogen.
  • a further object of this invention is to provide NMR images of the projection of specific portions of a volume.
  • two-dimensional projection images are formed representing different NMR components within the body. These are processed to produce projection images of specific materials, with the intervening materials removed. Also, projection images are obtained of specific regions within the body.
  • Figure 1 is a schematic drawing illustrating an embodiment of the invention:
  • Fig. 1 An understanding of the broad aspects of the invention may best be had by reference to Fig. 1.
  • 11 can represent a bone structure which it is desired to visualize.
  • bone structure 11 may be interfering with the visualization of soft tissue structure 12. which can represent the liver, kidneys, brain, etc. Also, it is often important to visualize regions of disease such as is illustrated by tumor 32 imbedded in soft tissue structure 12.
  • the principal axial magnetic field is produced usitig, for example, pole pieces 13 and 14 excited by coils 16 and 17. These are driven by a d.c. source V J with the coils 16 and 17 producing fields in the same direction to create a substantially uniform field throughout the region of interest in volume 10. This is by far the strongest field in the system with a strength of the order of one kilogauss. With both this coil and the remaining coils, the letter pairs A-D are simply convenient ways of indicating connections.
  • Coils 18 and 19 form a gradient field in the z direction driven by 20, source V 2 .
  • coils 23 and 24 are on opposite sides of object 10 and thus form a gradient field in the z direction driven by 25, source V 3 .
  • these gradient coils are bucking each other so as to produce a varying field in the respective direction.
  • Coils 21 and 22 are the radio frequency coils serving both the transmitter and receiver function. They produce fields in the same direction to create a substantially uniform field in volume 10.
  • generator V 4 is used to excite the magnetic spins in volume 10.
  • signal 31 is received from magnetic spin signals in volume 10.
  • processor 29 receives signals from magnetic spin signals in volume 10.
  • excitation signals V 4 and processing systems 29 can be used to isolate specific materials, organs or lesions in volume 10.
  • the projections of these isolated structures, projected onto plane 28, are displayed in display 30.
  • projections of the volume are obtained which are functions of p, T 1 , and T z , which are respectively the spin density, the spin-lattice or longitudinal relaxation time and the spin-spin or transverse relaxation time.
  • p, T 1 , and T z which are respectively the spin density, the spin-lattice or longitudinal relaxation time and the spin-spin or transverse relaxation time.
  • Each material has a unique set of these three parameters.
  • a number of measurement techniques are used to provide different functional relationships f n of these parameters. These can then be combined to, for example, eliminate any material k which has a given set p k .
  • T 1k and T 2k can be combined to enhance and/or isolate any material which has a given set of these parameters. This capability allows projection imaging to be used to its fullest advantage; by isolating the region of interest and removing intervening structures.
  • the Z a and Z b images can be used to cancel specific materials which are mixtures of these two components. For example, assume a lesion or organ material has a ratio r of Z a to Z b . Then an image with this lesion cancelled Z 1 can be provided as given by In addition to cancelling some specific material, this approach can also be used for evaluating an unknown material, such as in determining whether a tumor is benign or malignant. A control can be placed on the ratio r. While observing the display, the clinician can vary this control until the lesion disappears. The resultant ration r is indicative of the material properties of the tumor.
  • the transverse or spin-spin relaxation time T 2 is measured by first using a 90° excitation for V 4 providing a free induction decay. The intensity of this signal is the previously indicated I 1 . After a time t b , a 180° inversion is applied. This causes those signal phases caused by nonuniform magnetic fields to reverse and begin to move in phase, producing a spin echo signal at 2t b . The intensity of this signal I 8 is given by where This additional piece of information can also be used to obtain isolated images of Z a (x,y) and Z b (x,y). More important, it can be used to isolate a third material Z c . For example, the three measurements I 1 ,I 2 , and Is can be used to make isolated projection images of the bone 11. soft tissue organ 12 and tumor 32 in volume 10.
  • pulse generator 40 produces various pulse sequences 41. These are used to provide modulated radio frequency bursts which provide the excitation waveforms V 4 . These radio frequency bursts can either be narrowband or wideband depending on the type of imaging system used. These will be subsequently discussed.
  • Figure 2 illustrates the pulse sequences V 4 , the associated angles of the magnetic moment 6 and the resultant received signals 31.
  • a burst from modulator 42 results in a 90° excitation signal.
  • the received free induction decay signal is shown in Fig. 2a indicating the line integral of the density.
  • Pulse 47 is applied to sample and hold structure 43 which records the peak amplitude of the free induction decay signal I 1 and stores it.
  • a measurement related to T 1 is obtained as shown in Fig. 2b using a 180° excitation burst followed, after a time t. by a 90° burst.
  • the peak of the resultant FID signal I 2 is again sampled and stored.
  • Figure 2c illustrates the sequence used to develop a measurement indicative of T 2 .
  • a 90° excitation pulse is used.
  • the resultant FID signal can be ignored or it can be measured as an alternative method of deriving 1 1 .
  • pulse generator 40 and modulator 42 are used to produce a 180° inversion excitation. This causes the misphased spins to reverse and begin to form in phase.
  • the spins realign at time 2t b producing a spin echo signal.
  • the peak of this signal I s is stored in sample and hold system 43.
  • the effective parameters of the moving blood, p, T 1 and T z experience significant changes. This makes it possible to cancel all material. such as bone and soft tissue, except the moving blood.
  • the resultant images are isolated projection images of blood vessels. These are very significant in the diagnosis of stenosis or narrowrings of vessels which is a major disease.
  • received signal 31 is applied to bandpass filters 50, 51 and 52. These each have center frequencies corresponding to the element or isotope being imaged. These are passed onto sample and hold circuits 43. 53, 54, each identical to those previously described where the peak of an FID signal or a spin-echo signal is measured and stored corresponding to functions of p, T, and T 2 . Thus three measured intensities are established for each element or isotope. In the particular example where three elements or isotopes are used, we have 9 independent parameters defining the materials. These are then applied to algebraic inverter 44 which inverts the 9 x 9 matrix and provides a high degree of material selectivity. The resultant material signals can be used to provide a high degree of chemical analysis where a wide range of otherwise similar materials can be cancelled or enhanced in the image.
  • the various elements and isotopes are studied simultaneously. In many cases, however, it is desirable to use a high axial magnetic field for elements other than hydrogen. In that case the signals from the various elements and isotopes can be acquired in sequence where the axial magnetic field is changed for each element. Thus V 1 is increased for elements other than hydrogen.
  • V 4 excitation signal must include energy at that frequency so that signal 31 can include the required FID or spin echo signals corresponding to that element.
  • Projection images can be accomplished in a variety of ways, using the basic structure of Fig. 1.
  • an array of planar integrals are formed, each being perpendicular to the projection plane 28.
  • the signals from a set of parallel planes are acquired.
  • the angle of the planes are determined by the direction of the gradient field.
  • the total gradient field is a combination of the gradient field in the z direction, driven by signal V 2 using coils 18 and 19, and the field in the x direction, driven by signal V s using coils 23 and 24.
  • Processor 29 then includes a Fourier transform system, such as a digital FFT (Fast Fourier Transform), to separately extract the signals from each of the parallel planes. This process is repeated with a voltage applied to V 3 . with V 2 zero, providing information about a parallel set of yz planes, each perpendicular to the x-axis. Sets of planes at intermediate angles are acquired by simply using voltage combinations on V 2 and V 3 to provide gradients at intermediate angles.
  • a Fourier transform system such as a digital FFT (Fast Fourier Transform)
  • processor 29 consists of a Fourier transform system to provide the planar signals at all angles, a storage system to store the values at each angle, and a reconstructor to reconstruct the two-dimensional projection image.
  • a preferred embodiment involves the same basic structure in Fig. 1.
  • the information for a complete line in projection image 28, representing the lines in a plane in volume 10 can be acquired.
  • the gradient field in the z direction is made time-varying by making V 2 an a.c. or time-varying signal.
  • One zy plane, perpendicular to the z axis, will not be time-varying since it will be at the null of the gradient field.
  • Received signal 31 will receive NMR signals from that null plane since the others will not receive the correct excitation.
  • the time-varying gradient can be applied in the transmit and/or the receive mode to average out all but the null plane.
  • Processor 29 includes a Fourier transform system for taking a transform of the signals from the null plane. Decomposing the signal into different frequencies provides the signals from each line in the plane, or each point in the line on projection plane 28. Thus the output of the Fourier transform system directly provides an array of points along a line in the projection image.
  • the null plane is determined by that plane where the gradient field induced by a.c. signal Y z is zero. As shown in Fig. 1, with the B terminal on coil 18 connected to the B terminal on coil 19, the null plane will be exactly between the coils since they are driven out of phase. To move the position of the null plane we can ground the upper B terminal on coil 18, and connect a signal kV 2 to the lower B terminal on coil 19. With k equal to unity, the null plane will again be between the coils. However, by making k greater than or less than unity, the null plane will move higher and lower respectively. Thus any desired plane can be selected to provide the desired horizontal line image on projection plane 28.
  • Motion considerations are considerably improved with this data acquisition system. Since the projection image is acquired a line at a time, blurring considerations are based on the acquisition time of each line, rather than the time of the entire image. This approach is therefore preferable in regions of the body, such as the heart, where rapid motions are involved.
  • the two projection imaging systems just described can be used with any of the previously described systems for measuring the projected amount of components for the materials in volume 10.
  • the excitations shown in Figs. 2b and 2c can replace the wideband excitations previously described where an array of parallel planes or parallel lines are simultaneously excited.
  • All of the pulse waveforms shown in Figs. 2b and 2c can be replaced by wideband waveforms which simultaneously provide 90° or 180° excitation over a band of frequencies. These waveforms will have envelopes which have the classic sin x/x shape so that their Fourier transforms will be flat spectra in the regions of interest.
  • Signal 31 will first be applied to a Fourier transform system to provide an array of signals, each representing a specific frequency region.
  • Each signal will be applied to a sample and hold system 43, using the timing shown in Figs. 2b and 2c, to provide I 1 , I 2 and Is for each frequency representing each projected region of the volume.
  • Fig. 3 represents the processing for one plane in the volume for the first projection imaging system or for one line in a plane of the second projection imaging system using the time-varying gradient.
  • An alternate data acquisition system makes use of the intersection of excited planes.
  • An inversion excitation of 180" inverts the angle of the magnetic spin moment and produces no free induction decay signal.
  • a specific plane, normal to the projection plane 28, can be excited. This plane can then be decomposed into individual lines using the intersection with an array of orthogonal planes, each provided with inversion excitation.
  • the selected plane into an array of individual lines perpendicular to the projection plane 28.
  • the array of lines are formed by an array of yz planes intersecting the saturated xy planes.
  • This array of planes are formed by first applying a voltage V 3 to provide a gradient in the x direction so that each yz plane corresponds to a different resonant frequencies.
  • a broadband inverting excitation is then applied using V 4 . This inverting or 180" excitation will only produce an output at the intersection with the excited zy plane.
  • the resultant spin echo decay signal 31 is a broadband signal representing the array of intersection lines in the excited xy plane.
  • Processor 29 includes a Fourier transform system for decomposing the signal into its frequency components representing each of the lines of intersection. Each of these lines represents the projection value of a point on projection plane 28. This sequence is repeated for each xy plane by merely changing the frequency of the burst signal V 4 when the plane is selected. Thus the complete projection image is formed.
  • This projection imaging system essentially uses the sequence shown in Fig. 2c where each isolated line of intersection is subjected to a 90° and then 180° excitation, where the amplitude of the spin echo signal I s represents the line integral of a specific component.
  • the I 1 signal shown in Fig. 2c cannot be used since it is a part of a planar coincidence sequence which isolated the line. Therefore, measurements of I 1 and 1 2 . will have to be accomplished by one of the other projection imaging sequences.
  • a similar projection imagiag system can be used based on a paper by P. Mansfield, A.A. Maudsley and T. Baines entitled, "Fast Scan Proton Density Imaging by NMR,” which appeared in the Journal of Physics E: Scierrtific Instruments, 1976, Vol. 9, pp. 271-278.
  • a shaped pulse is used which excites all planes but one section with a 90° spin moment.
  • another 90° excitation is used. Only the intersection of the two planes produces a received signal following the second excitation.
  • a pulse excitation V 4 is used of the form where where fo is the center frequency representing the plane being addressed, b represents the thickness of the desired section and a represents the thickness of the entire volume.
  • fo the center frequency representing the plane being addressed
  • b the thickness of the desired section
  • a the thickness of the entire volume.
  • the excited field is the difference of the two rectangular functions, the large one representing the size of the volume ⁇ , and the small one the section thickness b.
  • a gradient normal to the xy plane is produced by applying a voltage V 3 .
  • V 4 With this gradient a broadband pulse V 4 is used which simultaneously excites all of the _ spin moments in the selected xy plane to the 90° level.
  • the resultant free induction decay signal is Fourier transformed to provide the projection of the lines in the selected plane only. This sequence is then repeated with a new gradient in the z direction to select a new plane.
  • the amplitude of the free induction decay signal following the second 90° excitation, as in Fig. 2a, represents the desired signal I 1 .
  • this signal is Fourier transformed to simultaneously provide the I 1 value for each line in the selected plane.
  • This same imaging approach can be used to measure I 3 as shown in Fig. 2c.
  • a 180° broadband burst is used following a time period t b as shown.
  • the spin echo signal occurring at 2t b is then Fourier transformed to provide the I 3 value for all lines.
  • this imaging approach can provide the I 1 and Is projected signals for each line. These are processed, as in Fig. 3, to provide material images.
  • the final projection imaging method is based on the spin warp imaging method previously described. This is similar to the previous method in that an excited xy plane is decomposed into individual lines.
  • the method of decomposition is distinctly different.
  • a gradient normal to the plane Prior to exciting the selected xy plane with burst signal V 4 , a gradient normal to the plane is applied using voltage V 3 . This has the affect of periodically "warping" the phase along the x direction.
  • the resultant received signal therefore represents periodic variations in the x direction within the excited xy plane.
  • the spatial frequency of these periodic variations can be altered by changing the strength of the gradient, as represented by voltage V 3 .
  • Processor 29 can include an inverse Fourier transform to convert this spatial frequency decomposition into the desired line components perpendicular to the projection image 28.
  • this system through a sequence of excitations, resulted in the decomposition of the excited plane into lines. As before, this can be repeated for all xy planes. This, however, would represent a relatively long data acquisition time.
  • a preferred approach is the use of a broadband excitation signal V 4 which simultaneously excites all of the parallel xy planes. Again, these are each of different frequencies because of the gradient in the z direction introduced by V 2 .
  • the phase warping gradient in the x direction, produced by V 3 will now be simultaneously applied to all zy planes at their individual frequencies.
  • the individual planes are separated in processor 29 using the previously described Fourier transform system to separate the individual frequencies corresponding to each plane.
  • a temporal Fourier transform separates the individual xy planes and a spatial inverse Fourier transform decomposes the lines in the planes.
  • This spin warp projection imaging system can be used with each of the projection measurement systems of Figs. 2a, 2b, and 2c.
  • the signal is temporally Fourier transformed to divide the signal into different planes.
  • Each planar signal is decomposed into lines using the sequence of spatial patterns followed by a spatial Fourier transform. This provides the I 1 signal for each line in the volume, corresponding to a point on projection plane 28.
  • the single broadband 90° excitation can be replaced by the sequences of Figs. 2b and 2c, again using broadband excitation for both the 90° and 180° bursts. Then transformed, these provide the desired I 1 ,I 2 and Is signals for the integral or projection of each line in volume 10.
  • the measurements made can be made at each frequency band corresponding to each element on isotope. That is, referring to Fig. 4, the various operations performed on signal 31, for a specific element, can be performed on signals 55,56 and 57 for a variety of isotopes and elements which resonate at different frequencies.
  • each projection system is used to provide line integral measurements of different components of the different materials.
  • Each of the basic data acquisition systems described have been used as parts of complex data acquisition systems to provide three-dimensional cross-sectional images.
  • these data acquisition systems have been modified to provide two-dimensional projection images of the volume 10 with all of the aforementioned advantages of faster data acquisition, better SNR, higher resolution, less sensitivity to artifacts, relaxed requirements on the uniformity of the magnetic fields and a much larger and more appropriate field of view.
  • projections were obtained at a specific projection angle in the y direction onto plane 28.
  • an additional set of coils can be used perpendicular to coils 23 and 24 and parallel to projection plane 28. These can be used, in lieu of coils 23 and 24, to provide a projection image in an orthogonal plane.
  • undesired intervening structures were removed by taking weighted sums of specific components of the projection images.
  • An alternate general approach is to acquire projection measurements of portions of volume 10, thus avoidiag the undesired intervening structures.
  • One general approach is not including these undesired structures in the excited magnetic volume. This can be accomplished by using relatively small coils, 16 and 17 for producing the static field, and positioning them so as to excite only the field of interest. For example, they could be positioned to avoid exciting bony structure 11. This approach has the undesired result of various image distortions produced by fringing fields. These are not too severe, however, in projection imaging systems.
  • a preferable approach is the size and placement of the r.f. excitation coils 21 and 22. These can be placed in any position as long as the axis of the two coils is perpendicular to the z axis. Thus they can be rotated around the z axis and shifted laterally to avoid exciting an undesired intervening structure.
  • Coils 21 and 22 instead of being driven equally as in Fig. 1, can be driven to provide a gradient of excitation.
  • Point D on coil 21 can be grounded, with point D on coil 22 driven by kV 4 .
  • the gradient in intensity will depend on k where k is greater than or less than unity, depending on the desired gradient direction.
  • the gradient can be arranged such that the undesired portion of the volume experiences the 180° inversion and produces no signal.
  • Another arrangement is a gradient varying in phase from 0° on one end to 180° on the other. In this case the central region of the volume, having the required 90° excitation, will provide a projection image with the end regions producing no decay signal.
  • More elaborate systems can be used employing sequences of excitation having coarse periodic variations. These can then be stored and combined and used to select any region of volume 10. It should be emphasized, however, that a relatively few such excitations are required as compared to systems employing three-dimensional imaging.
  • the spatial selectivity can be improved by acquiring one or two more signals with different B 1 gradients.
  • a second set of excitation waveforms on coils 22 and 23 so that the magnetic moment angle goes from -270° to +270°.
  • a third excitation not shown, providing a fifth harmonic distribution where the phase varies from -450° to 450°.
  • the result of these two or more excitations can be added, in appropriate weights, to limit the region of excitation to the center of the volume, as shown in curve 62, in Fig. 5.
  • a large variety of variations on this theme can be used to isolate regions of volume 10 using gradients of the B 1 excitation.
  • the selective excitation method described produces a single projection component. I 1 . In many cases this will prove sufficient since the removal of intervening structures is being accomplished by selectively exciting portions of the volume rather than eliminating structures having specific material properties. In many cases, however, it will be desirable to accomplish both selective excitation and material cancellation or enhancement. For example, referring to Fig. 1, it may prove desirable to eliminate bone 11 through selective excitation, but to isolate or analyze tumor 32 through material enhancement or cancellation.
  • the other important components, I 2 and Is can be derived using gradient excitation by making use of the property that various portions of the projection are at 90° or 180°.
  • each selective gradient excitation after a time t we follow each selective gradient excitation after a time t, with an additional gradient excitation where a 90° excitation is added at each point.
  • each 90° region now becomes 180°, thus producing a spin echo at time 2t b .
  • the projection I 3 can be obtained.
  • a 90 8 excitation added at each point, and excite it after t a seconds with the additional 90° removed we produce the excitation sequence of Fig. 2b.
  • the 90° regions will be at 180°, so that the removal of a 90° excitation after t a seconds will produce an FID signal whose peak amplitude is I 2 .
  • the measurements I 1 .I 2 and Is are combined, as previously described, to select specific materials within the selected volume.
  • V 4 can be a saturation pulse having a frequency content representing those regions of volume 10 where the projection image is not desired. The pulse contains no energy at those frequencies corresponding to the desired regions of volume 10.
  • V 4 signal can be of the form where fo is the center frequency representing the center of the volume of interest, D represents the frequency range corresponding to the portion of the volume where projection imaging is desired, and C represents the entire frequency range of the volume where C > D.
  • fo the center frequency representing the center of the volume of interest
  • D the frequency range corresponding to the portion of the volume where projection imaging is desired
  • C represents the entire frequency range of the volume where C > D.
  • V 4 signal is applied in the presence of a static gradient introduced by coils 18 and 19, and/or coils 23 and 24.
  • any projection imaging system can be used on the unsaturated volume. Again, the projection imaging system can be used with any of the component selective systems of Figs. 2a, 2b or 2c.
  • the techniques used in three-dimensional reconstructions can be used in a limited form to restrict the volume over which the two-dimensional projection is obtained.

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EP82306733A 1981-12-21 1982-12-16 Système de formation d'images pour la projection sélective de matériau utilisant la RMN Expired EP0086306B1 (fr)

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US332926 1981-12-21
US06/332,926 US4486708A (en) 1981-12-21 1981-12-21 Selective material projection imaging system using nuclear magnetic resonance

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EP0091556A2 (fr) * 1982-03-18 1983-10-19 Bruker Medizintechnik GmbH Procédé de mesure de la résonance magnétique nucléaire pour la tomographie NMR
DE3617659A1 (de) * 1985-05-29 1986-12-04 Yokogawa Hokushin Electric Corp., Musashino, Tokio/Tokyo Nmr-abbildungsgeraet
EP0260426A1 (fr) * 1986-08-18 1988-03-23 Siemens Aktiengesellschaft Méthode pour l'obtention des spectres de résonance magnétique nucléaire d'une région localisée sélectivement à l'interieur d'un échantillon étudié
US5467016A (en) * 1993-04-20 1995-11-14 Siemens Medical Systems, Inc. Saturation selective spectroscopic imaging
CN108872897A (zh) * 2018-04-19 2018-11-23 上海市东方医院 核磁共振t2图像成像方法
CN110308311A (zh) * 2019-07-16 2019-10-08 东北大学 一种基于二维旋转机控的三维磁场发生装置

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JPS5985651A (ja) * 1982-11-08 1984-05-17 株式会社東芝 診断用核磁気共鳴装置
JPS59146641A (ja) * 1983-02-10 1984-08-22 株式会社日立製作所 医用核磁気共鳴イメ−ジング装置の関心領域撮影方式
US4551680A (en) * 1983-04-21 1985-11-05 Albert Macovski Selective region NMR projection imaging system
JPS6085357A (ja) * 1983-10-17 1985-05-14 Toshiba Corp 核磁気共鳴映像装置
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US4581582A (en) * 1983-12-27 1986-04-08 General Electric Company High-spatial-resolution spectroscopic NMR imaging of chemically-shifted nuclei
EP0164142B1 (fr) * 1984-05-02 1991-03-27 Koninklijke Philips Electronics N.V. Procédé et dispositif pour déterminer la distribution de la magnétisation nucléaire dans une région d'un corps
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DE3570135D1 (en) * 1984-08-01 1989-06-15 Siemens Ag Apparatus for producing images of an object under examination
US4618827A (en) * 1984-09-10 1986-10-21 General Electric Company Method for high-spatial-resolution spectroscopic NMR imaging of chemically-shifted nuclei
US4656424A (en) * 1984-11-07 1987-04-07 Yuval Tsur Apparatus and methods for selective excitation
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JP2960419B2 (ja) * 1988-08-10 1999-10-06 株式会社日立製作所 磁気共鳴イメージング方法
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Cited By (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0091556A2 (fr) * 1982-03-18 1983-10-19 Bruker Medizintechnik GmbH Procédé de mesure de la résonance magnétique nucléaire pour la tomographie NMR
EP0091556A3 (en) * 1982-03-18 1986-07-23 Bruker Medizintechnik Gmbh Method of measuring nuclear magnetic resonance for application to nmr tomography
DE3617659A1 (de) * 1985-05-29 1986-12-04 Yokogawa Hokushin Electric Corp., Musashino, Tokio/Tokyo Nmr-abbildungsgeraet
EP0260426A1 (fr) * 1986-08-18 1988-03-23 Siemens Aktiengesellschaft Méthode pour l'obtention des spectres de résonance magnétique nucléaire d'une région localisée sélectivement à l'interieur d'un échantillon étudié
US4816764A (en) * 1986-08-18 1989-03-28 Siemens Aktiengesellschaft Method for the identification of nuclear magnetic spectra from spatially selectable regions of an examination subject
US5467016A (en) * 1993-04-20 1995-11-14 Siemens Medical Systems, Inc. Saturation selective spectroscopic imaging
CN108872897A (zh) * 2018-04-19 2018-11-23 上海市东方医院 核磁共振t2图像成像方法
CN108872897B (zh) * 2018-04-19 2021-05-21 上海市东方医院 核磁共振t2图像成像方法
CN110308311A (zh) * 2019-07-16 2019-10-08 东北大学 一种基于二维旋转机控的三维磁场发生装置

Also Published As

Publication number Publication date
US4486708A (en) 1984-12-04
JPS58154647A (ja) 1983-09-14
JPH0616755B2 (ja) 1994-03-09
DE3275486D1 (en) 1987-04-02
EP0086306B1 (fr) 1987-02-25

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